Monitoring device, method and system

ABSTRACT

A monitoring device ( 20 ) for monitoring the vital signs of a user is disclosed herein. The monitoring device ( 20 ) is preferably an article ( 25 ) having an optical sensor ( 30 ) and a circuitry assembly ( 35 ). The monitoring device ( 20 ) preferably provides for the display of the following information about the user: pulse rate; blood oxygenation levels; calories expended by the user of a pre-set time period; target zones of activity; time; distance traveled; and/or dynamic blood pressure. The article ( 25 ) is preferably a band worn on a user&#39;s wrist, arm or ankle.

CROSS REFERENCES TO RELATED APPLICATIONS

The Present application is a continuation-in-part application of U.S.patent application Ser. No. 11/388,707, filed on Mar. 24, 2006, whichclaims priority to U.S. Provisional Application No. 60/665,116, filed onMar. 25, 2005 and which is a continuation-in-part application of U.S.patent application Ser. No. 11/085,778, filed on Mar. 21, 2005, whichclaims priority to U.S. Provisional Application No. 60/613,785, filed onSep. 28, 2004, now abandoned. The Present Application also claimspriority to U.S. Provisional Application No. 60/843,967, filed on Sep.12, 2006 and U.S. Provisional Application No. 60/829,679, filed on Oct.17, 2006.

STATEMENT REGARDING FEDERALLY SPONSORED RESEARCH OR DEVELOPMENT

Not Applicable

BACKGROUND OF THE INVENTION

1. Field of the Invention

The present invention is related to real-time vital sign monitoringdevices. More specifically, the present invention relates to a wrist,arm or ankle band for monitoring a user's vital signs, and a system thatuses the monitoring device to display a real-time vital sign of anathlete/player during an event.

2. Description of the Related Art

There is a need to know how one is doing from a health perspective. Insome individuals, there is a daily, even hourly, need to know one'shealth. The prior art has provided some devices to meet this need.

One such device is a pulse oximetry device. Pulse oximetry is used todetermine the oxygen saturation of arterial blood. Pulse oximeterdevices typically contain two light emitting diodes: one in the red bandof light (660 nanometers) and one in the infrared band of light (940nanometers). Oxyhemoglobin absorbs infrared light while deoxyhemoglobinabsorbs visible red light. Pulse oximeter devices also contain sensorsthat detect the ratio of red/infrared absorption several hundred timesper second. A preferred algorithm for calculating the absorption isderived from the Beer-Lambert Law, which determines the transmittedlight from the incident light multiplied by the exponential of thenegative of the product of the distance through the medium, theconcentration of the solute and the extinction coefficient of thesolute.

The major advantages of pulse oximetry devices include the fact that thedevices are non-invasive, easy to use, allows for continuous monitoring,permits early detection of desaturation and is relatively inexpensive.The disadvantages of pulse oximetry devices are that it is prone toartifact, it is inaccurate at saturation levels below 70%, and there isa minimal risk of bums in poor perfusion states. Several factors cancause inaccurate readings using pulse oximetry including ambient light,deep skin pigment, excessive motion, fingernail polish, low flow causedby cardiac bypass, hypotension, vasoconstriction, and the like.

Chin et al., U.S. Pat. No. 6,018,673 discloses a pulse oximetry devicethat is positioned entirely on a user's nail to reduce out of phasemotion signals for red and infrared wavelengths for use in a leastsquares or ratio-of-ratios technique to determine a patient's arterialoxygen saturation.

Smith, U.S. Pat. No. 4,800,495 discloses an apparatus for processingsignals containing information concerning the pulse rate and thearterial oxygen saturation of a patient. Smith also disclosesmaintaining the position of the LEDs and detectors to preventmotion-artifacts from being produced in the signal.

Another method for using a pulse oximeter to measure blood pressure isdisclosed in U.S. Pat. No. 6,616,613 to Goodman for a ‘PhysiologicalSignal Monitoring System’. The '613 patent discloses processing a pulseoximetry signal in combination with information from a calibratingdevice to determine a patient's blood pressure.

Chen et al, U.S. Pat. No. 6,599,251 discloses a system and method formonitoring blood pressure by detecting pulse signals at two differentlocations on a subjects body, preferably on the subject's finger andearlobe. The pulse signals are preferably detected using pulse oximetrydevices.

Schulze et al., U.S. Pat. No. 6,556,852, discloses the use of anearpiece having a pulse oximetry device and thermopile to monitor andmeasure physiological variables of a user.

Malinouskas, U.S. Pat. No. 4,807,630, discloses a method for exposing apatient's extremity, such as a finger, to light of two wavelengths anddetecting the absorbance of the extremity at each of the wavelengths.

Jobsis et al., U.S. Pat. No. 4,380,240 discloses an optical probe with alight source and a light detector incorporated into channels within adeformable mounting structure which is adhered to a strap. The lightsource and the light detector are secured to the patient's body byadhesive tapes and pressure induced by closing the strap around aportion of the body.

Tan et al., U.S. Pat. No. 4,825,879 discloses an optical probe with aT-shaped wrap having a vertical stem and a horizontal cross bar, whichis utilized to secure a light source and an optical sensor in opticalcontact with a finger. A metallic material is utilized to reflect heatback to the patient's body and to provide opacity to interfering ambientlight. The sensor is secured to the patient's body using an adhesive orhook and loop material.

Modgil et al., U.S. Pat. No. 6,681,454 discloses a strap that iscomposed of an elastic material that wraps around the outside of anoximeter probe and is secured to the oximeter probe by attachmentmechanisms such as Velcro, which allows for adjustment after initialapplication without producing excessive stress on the spring hinge ofthe oximeter probe.

Diab et al., U.S. Pat. No. 6,813,511 discloses a disposable opticalprobe suited to reduce noise in measurements, which is adhesivelysecured to a patient's finger, toe, forehead, earlobe or lip.

Diab et al., U.S. Pat. No. 6,678,543 discloses an oximeter sensor systemthat has a reusable portion and a disposable portion. A method forprecalibrating a light sensor of the oximeter sensor system is alsodisclosed.

Tripp, Jr. et al., U.S. Statutory Invention Registration Number H1039discloses an intrusion free physiological condition monitor thatutilizes pulse oximetry devices.

Hisano et al., U.S. Pat. No. 6,808,473, discloses a headphone-typeexercise aid which detects a pulse wave using an optical sensor toprovide a user with an optimal exercise intensity.

Mathews, U.S. Pat. No. 5,431,170 (“Mathews”), discloses a pulseresponsive device, which has a pulse oximetry device (10) attached to aheadband (12) and a separate read-out device (14) that may be attachedto a glove and worn on the user's hand. Mathews discloses that theread-out device (14) has a digital display and an analogue display,however, Mathews provides no further detail.

Mault et al, U.S. Patent Application Publication Number 2002/0109600(“Mault”) discloses a smart activity monitor (“SAM”) which is apedometer based device which includes an electronic clock, a sensor,entry means for recording food consumption and exercise activities and amemory for storing such information. Mault fails to disclose the detailsof the display other than to mention that the SAM has a time display, anexercise display and a food display, with the exercise and food displayshaving a bar-graph style. Mault fails to disclose an optical sensor indetail, and only states that photo-plethysmography may be used todetermine the heart rate by a sensor provided on the rear of a wristmounted SAM.

Kopotic et al, U.S. Pat. No. 6,470,199, discloses a sock for positioningan optical probe.

Yasukawa et al., U.S. Pat. No. 5,735,800 (“Yasukawa”), discloses awrist-worn device which is intended for limited motion about the user'swrist. Yasukawa discloses an optical sensor that uses a blue LED with aphototransistor in conjunction with an analog to digital converter toprovide a digital signal to a data processing circuit.

In monitoring one's health there is a constant need to know how manycalories have been expended whether exercising or going about one'sdaily routine. A calorie is a measure of heat, generated when energy isproduced in our bodies. The amount of calories burned during exercise isa measure of the total amount of energy used during a workout. This canbe important, since increased energy usage through exercise helps reducebody fat. There are several means to measure this expenditure of energy.To calculate the calories burned during exercise one multiplies theintensity level of the exercise by one's body weight (in kilograms).This provides the amount of calories burned in an hour. A unit ofmeasurement called a MET is used to rate the intensity of an exercise.One MET is equal to the amount of energy expended at rest.

For example, the intensity of walking 3 miles per hour (“mph”) is about3.3 METS. At this speed, a person who weighs 132 pounds (60 kilograms)will burn about 200 calories per hour (60×3.3=198).

The computer controls in higher-quality exercise equipment can provide acalculation of how many calories are burned by an individual using theequipment. Based on the workload, the computer controls of the equipmentcalculate exercise intensity and calories burned according toestablished formulae.

The readings provided by equipment are only accurate if one is able toinput one's body weight. If the machine does not allow this, then the“calories per hour” or “calories used” displays are only approximations.The machines have built-in standard weights (usually 174 pounds) thatare used when there is no specific user weight.

There are devices that utilize a watch-type monitor to provide thewearer with heart rate as measured by a heartbeat sensor in a chestbelt.

The prior art has failed to provide a means for monitoring one's healththat is accurate, easy to wear on one's body for extended time periods,allows the user to input information and control the output, andprovides sufficient information to the user about the user's health.Thus, there is a need for a monitoring device that can be worn for anextended period and provide health information to a user.

Further, the viewers of an athletic event have always desired to haveinformation on the athletes' performance during the event. Recently,graphical displays during televised sporting events have included: thetrajectory of a hockey puck during a hockey game; the first down lineduring a football game; the location of birdies, bogeys and eagles for ahole during a golf tournament; and the out of bounds line during atennis match. Further, informational displays during televised sportingevents have included: the speed of a pitch during a baseball game; thespeed of a serve during a tennis match; the distance of a drive during agolf tournament; the money won and cards held by a poker player; and thenumber of punches thrown during a boxing match.

The modern viewer of athletic events demands a greater quantity ofinformation for the performance of the athlete. The modern viewer wantssufficient information of the athlete/player to vicariously participatein the event through the athlete/player.

BRIEF SUMMARY OF THE INVENTION

The present invention provides a solution to the shortcomings of theprior art. The present invention is accurate, comfortable to wear by auser for extended time periods, allows for input and controlled outputby the user, is light weight, and provides sufficient real-timeinformation to the user about the user's health. Further, the presentinvention allows for the transmission of a multitude of the user's realtime vital signs to a video display monitor during an athletic event toenhance the viewing enjoyment of the audience.

One aspect of the present invention is a monitoring device formonitoring the health of a user. The monitoring device includes anarticle, an optical device for generating a pulse waveform, a circuitryassembly embedded within the article, a display member positioned on anexterior surface of the article, and a control means attached to thearticle.

The article is preferably a band to be worn on a user's wrist or ankle.The article preferably has a minimal mass, one to five ounces, and isflexible so that the user can wear it the entire day if necessary. Themonitoring device allows the user to track calories burnt during a settime period, monitor heart rate, blood oxygenation levels, distancetraveled, target zones and optionally dynamic blood pressure.

Another aspect of the present invention is a method for monitoring auser's vital signs. The method includes generating a signalcorresponding to the flow of blood through an artery of the user. Thesignal is generated from an optical device. Next, the heart rate data ofthe user and an oxygen saturation level data of the user is generatedfrom the signal. Next, the heart rate data of the user and the oxygensaturation level data of the user are processed for analysis of caloriesexpended by the user and for display of the user's heart rate and bloodoxygen saturation level. Next, the calories expended by the user, theuser's heart rate or the user's blood oxygen saturation level aredisplayed on a display member on an exterior surface of an article,which is controlled by the user using a control component extending fromthe article.

Yet another aspect of the present invention is a system for real timemonitoring of a user's vital sign during a live event within a playingenvironment. The system includes a monitoring device, a computing deviceand an electro-optical display. The monitoring device is attached to anarm, wrist or ankle of the user. The monitoring device comprises meansfor generating a real-time vital sign signal corresponding to the heartrate of the user, and means for transmitting the real-time vital signsignal outside of the playing environment. The computing device ispositioned outside of the playing environment. The computing devicecomprises means for receiving the real-time vital sign signal from themonitoring device, and means for processing the real-time vital signsignal for transmission to and image on the electro-optical display.

Yet another aspect of the present invention is a monitoring device formonitoring the health of a user. The monitoring device includes anarticle to be worn on the user's wrist, arm or ankle. The monitoringdevice also includes an optical sensor, a circuitry assembly, a displaymember and a control component. The optical sensor is disposed on theinterior surface of the article. The circuitry assembly is preferablyembedded within the annular body of the article. The display member ispreferably attached to an exterior surface of the annular body of thearticle. The control component is disposed on the exterior surface ofthe annular body of the article. The control component controls theinput of information and the output of information displayed on thedisplay member.

Having briefly described the present invention, the above and furtherobjects, features and advantages thereof will be recognized by thoseskilled in the pertinent art from the following detailed description ofthe invention when taken in conjunction with the accompanying drawings.

BRIEF DESCRIPTION OF THE SEVERAL VIEWS OF THE DRAWINGS

FIG. 1 is a plan view of a preferred embodiment of a monitoring deviceworn by a user.

FIG. 2 is a perspective view of the article of the monitoring deviceworn by a user.

FIG. 2A is a plan view of the article of the monitoring device.

FIG. 2B is a front side view of the article of the monitoring device.

FIG. 2C is a rear side view of the article of the monitoring device.

FIG. 2D is an edge side view of the article of the monitoring device.

FIG. 2E is a bottom plan view of the article of the monitoring device.

FIG. 3 is a top view of an alternative embodiment of the monitoringdevice of the present invention.

FIG. 3A is bottom view of the monitoring device of FIG. 3.

FIG. 3B is a top perspective view of the monitoring device of FIG. 3worn on a user's arm.

FIG. 4 is a schematic view of arteries within a human arm.

FIG. 5 is a front view of a user running on exercise equipment with themonitoring device on her arm.

FIG. 6 is an isolated view of a display unit of the exercise equipmentof FIG. 5.

FIG. 7 is a schematic flow chart of the signal acquisition step of theflow chart of FIG. 10.

FIG. 8 is a schematic view of the display member circuitry.

FIG. 9 is a schematic view of the circuitry assembly.

FIG. 10 is a flow chart of a signal processing method of the presentinvention.

FIG. 11 is an illustration of the waveforms of the data sampling duringthe signal processing method.

FIG. 12 is a flow chart of a portion of the signal processing steputilizing a motion sensor to reduce the affect of motion.

FIG. 13 is a flow chart of a noise reduction method of the presentinvention.

FIG. 14 is a flow chart of a specific noise reduction method of thepresent invention.

FIG. 15 is a schematic diagram of a prior art connection of a processorto an optical sensor.

FIG. 16 is a schematic diagram of a connection of a processor to anoptical sensor utilized by the present invention.

FIG. 17 is a schematic diagram of a light source intensity controllingmechanism of the present invention.

FIG. 17A is a schematic diagram of the light source intensitycontrolling mechanism of FIG. 17 with a single resistor connected.

FIG. 17B is a schematic diagram of the light source intensitycontrolling mechanism of FIG. 17 with two resistors connected.

FIG. 17C is a schematic diagram of the light source intensitycontrolling mechanism of FIG. 17 with all resistors connected.

FIG. 18 is a flow chart of a light source intensity controlling methodof the present invention.

FIG. 19 is a graph illustrating the method and mechanism of controllingthe intensity of the light source over time.

DETAILED DESCRIPTION OF THE INVENTION

As shown in FIGS. 1-2E, monitoring device is generally designated 20.The monitoring device 20 preferably includes an article 25 and anattachment band 26, preferably composed of first strap 26 a and secondstrap 26 b. The straps 26 a and 26 b are preferably attached to eachother with a VELCRO® hook and loop material. The article 25 preferablyincludes an optical sensor 30, a circuitry assembly 35, controlcomponents 43 a-43 c and optionally a display member 40. The monitoringdevice 20 is preferably worn on a user's wrist 71, arm 72 or ankle 73.The article 25 preferably has a housing 95 that is sized to securelyattach to a user's wrist 71, arm 72 or ankle 73, and the housing has aninterior surface 98 and an exterior surface 99. The housing 95 alsopreferably has a pair of slots 96 a and 96 b for placement of the straps96 a and 96 b therethrough for attachment purposes.

It is desirous to adapt the monitoring device 20 to the anatomy of theuser's arm 72 or even the user's ankle. The strap 96 is preferablycomposed of neoprene, leather, synthetic leather, LYCRA, another similarmaterial, or a combination thereof. The article 25 is preferablycomposed of a semi-rigid or rigid plastic with a rubber-like orsemi-flex plastic bottom layer for contact with the user's body. Thebottom layer of the housing 95 may have a curve surface for contact witha user's body. The article 25 preferably has a mass ranging from 5 gramsto 50 grams. Preferably, the lower the mass of the article 25, the morecomfort to the user. The article 25 preferably has a thickness rangingfrom 5 mm to 10 mm, and is most preferably 6.5 mm. The bottom layer 95 apreferably has a thickness ranging from 3.0 mm to 5.0 mm, and mostpreferably is 3.3 mm. A top layer 95 a preferably has a thicknessranging from 2.0 mm to 5.0 mm, and most preferably is 2.63 mm. Amid-layer 95 c preferably has a thickness ranging from 0.25 mm to 1.0mm, and most preferably is 0.5 mm. The housing 95 preferably has awidth, W, ranging from 30 mm to 50 mm, more preferably from 35 mm to 45mm, and is most preferably approximately 40 mm. The housing 95preferably has a length, L, ranging from 40 mm to 65 mm, more preferablyfrom 50 mm to 60 mm, and is most preferably approximately 55 mm. Thearticle 25 preferably has a mass ranging from 5 grams to 50 grams, andmore preferably from 10 grams to 40 grams. The light weight of thearticle 25 provides for more comfort to the user.

The optical sensor 30 is preferably positioned on the interior surface98 of the housing 95 and electrically connected to the circuitryassembly 35.

The optical sensor 30 of the monitoring device 20 is preferablypositioned over the radial artery 77 or ulnar artery 77 a (as shown inFIG. 4) if the article 25 is worn on the user's arm 72. The opticalsensor 30 of the monitoring device 20 is preferably positioned over theposterior tibial artery of a user if the article 25 is worn on theuser's ankle. However, those skilled in the pertinent art will recognizethat the optical sensor may be placed over other arteries of the userwithout departing from the scope and spirit of the present invention.Further, the optical sensor 30 need only be in proximity to an artery ofthe user in order to obtain a reading or signal.

In a preferred embodiment, the optical sensor 30 is a single lightemitting diode (“LED”) 135 based on green light wherein the LED 135generates green light (λ˜500-600 nm), and a phtotodetector 130 detectsthe green light. Yet in an alternative embodiment, the optical sensor 30is a photodetector 130 and a single LED 135 transmitting light at awavelength of approximately 900 nanometers as a pulsed infrared LED. Yetfurther, the optical sensor is a combination of a green light LED and apulsed infrared LED to offset noise affects of ambient light andsunlight. As the heart pumps blood through the arteries in the user'sarm, ankle or wrist, blood cells absorb and transmit varying amounts ofthe light depending on how much oxygen binds to the cells' hemoglobin.The photodetector 30, which is typically a photodiode, detectsreflectance/transmission at the wavelengths (green, red or infrared),and in response generates a radiation-induced signal.

Alternatively, the optical sensor 30 is a pulse oximetry device with alight source 135 that typically includes LEDs that generate both red(λ˜660 nm) and infrared (λ˜900 nm) radiation. As the heart pumps bloodthrough the arteries in the arm, ankle or wrist of the user, blood cellsabsorb and transmit varying amounts of the red and infrared radiationdepending on how much oxygen binds to the cells' hemoglobin. Thephotodetector 130, which is typically a photodiode, detects transmissionat the red and infrared wavelengths, and in response generates aradiation-induced signal.

A preferred optical sensor 30 utilizing green light is a TRS1755 sensorfrom TAOS, Inc of Plano Tex. The TRS1755 comprises a green LED lightsource (567 nm wavelength) and a light-to-voltage converter. The outputvoltage is directly proportional to the reflected light intensity.Another preferred photodetector 130 is a light-to-voltage photodetectorsuch as the TSL260R and TSL261, TSL261R photodetectors available fromTAOS, Inc of Plano Tex. Alternatively, the photodetector 130 is alight-to-frequency photodetector such as the TSL245R, which is alsoavailable from TAOS, Inc. The light-to-voltage photodetectors have anintegrated transimpedance amplifier on a single monolithic integratedcircuit, which reduces the need for ambient light filtering. The TSL261photodetector preferably operates at a wavelength greater than 750nanometers, and optimally at 940 nanometers, which would preferably havea LED that radiates light at those wavelengths.

In a preferred embodiment, the circuit assembly 35 is flexible to allowfor the contour of the user's arm, wrist or ankle, and the movementthereof. The circuitry assembly and display member 40 are preferablyseparate components electrically connected within the housing 95. In oneembodiment, discussed below, the display member 40 is removed and thesignal is sent to a device such as a personal digital assistant, laptopcomputer, mobile telephone, exercise equipment, or the like for displayand even processing of the user's real-time vital signs information.

Alternatively, the circuitry assembly 35 includes a flexiblemicroprocessor board which is a low power, micro-size easily integratedboard which provides blood oxygenation level, pulse rate (heart rate),signal strength bargraph, plethysmogram and status bits data. Themicroprocessor can also store data. The microprocessor can process thedata to display pulse rate, blood oxygenation levels, calories expendedby the user of a pre-set time period, target zone activity, time anddynamic blood pressure. Further, microprocessor preferably includes anautomatic gain control for preventing saturation of the photodetector,which allows for the device to be used on different portions of thehuman body.

The display member 40 is preferably a light emitting diode (“LED”).Alternatively, the display member 40 is a liquid crystal display (“LCD”)or other similar display device. As shown in FIG. 8, the display member40 is an LED array which preferably has seven rows 49 a-49 g andseventeen columns 47 a-47 q. Further, LED array is angled to allow for agreater aspect ratio. The LED array allows for each column to beilluminated separately thereby giving the appearance of a movingdisplay. For example, if the term “200 calories expended” is displayedon the display member 40, the “2” of the “200” would preferably firstappear in column 47 q and then subsequently in each of the other columns47 p-47 a, from the right-most column to the left-most column therebygiving the appearance of the term scrolling along the display member 40.The terms or words alternatively scroll from left to right. Stillalternatively, all of the columns are illuminated at once or all flashin strobe like manner. Further, the user's real-time pulse waveform isdisplayed in motion on the display member 40 as a default setting. Thoseskilled in the pertinent art will recognize alternative methods ofdisplaying information on the display member 40 without departing fromthe scope and spirit of the present invention.

As shown in FIG. 9, a microprocessor 41 processes the signal generatedfrom the optical sensor 30 to generate the plurality of vital signinformation for the user which is displayed on the display member 40.The control components 43 a-c are connected to the circuit assembly 35to control the input of information and the output of informationdisplayed on the display member 40.

The monitoring device 20 is preferably powered by a power source 360positioned on the article 25. Preferably the power source is a battery.The power source 360 is preferably connected to the circuit assembly 35by positive wire 45 a and ground wire 45 b, and the ground wire 45 b andpositive wire 45 c are embedded within the article 25. The power source360 is preferably an AA or AAA disposable or rechargeable battery. Thepower source 360 is alternatively a lithium ion rechargeable batterysuch as available from NEC-Tokin. The power source 360 preferably has anaccessible port for recharging. The circuit assembly 35 preferablyrequires 5 volts and draws a current of 20- to 40 milliamps. The powersource 360 preferably provides at least 900 milliamp hours of power tothe monitoring device 20.

As shown in FIGS. 3, 3A and 3B, an alternative embodiment of themonitoring device 20 comprises a light shield 21 with the article 25disposed on an exterior surface 21 a of the light shield 21, and theoptical sensor 30 disposed on an interior surface 21 b of the lightshield 21. The light shield 21 is preferably composed of a light-weight,non-transparent (preferably opaque) cloth material. The light shield 21prevents or substantially eliminates environmental light frominterfering with the optical sensor 30 thereby reducing interferencewith the signal. In a preferred embodiment, the light shield 21 is blackin color. A user preferably wears the monitoring device 20 on the user'sarm 72 as shown in FIG. 3B, with a display member 40 visible to theuser. In this embodiment, the article 25 contains a circuitry assembly35, as discussed above, within the housing 95 of the article 25. Thedisplay member 40 is preferably a LED display monitor, and alternativelya LCD display monitor.

A connection wire arrangement 45 is shown in FIG. 16, wherein theconnection 45 between the microprocessor 41 of the circuitry assembly 35and the optical sensor 30 is preferably non-planar or non-straight inorder to reduce noise in the signal. The prior art connection assemblyis shown in FIG. 15 wherein the connection wire 45′ is straight andprone to noise due to movement of the circuitry assembly 35 relative tothe optical sensor 30, especially lateral movement. The presentinvention has a non-straight or non-planar connection wire 45 whichreduces noise due to movement of the circuitry assembly 35 relative tothe optical sensor 30. The alternating portions of the connection wire45 absorb the shock of lateral movement and oscillating movement of thecircuitry assembly 35 relative to the optical sensor 30.

The monitoring device 20 alternatively has a short-range wirelesstransceiver 36 b which is preferably a transmitter operating on awireless protocol, e.g. Bluetooth™, part-15, or 802.11. “Part-15” refersto a conventional low-power, short-range wireless protocol, such as thatused in cordless telephones. The short-range wireless transmitter 36 b(e.g., a Bluetooth™ transmitter) receives information from themicroprocessor and transmits this information in the form of a packetthrough an antenna. An external laptop computer or hand-held devicefeatures a similar antenna coupled to a matched wireless, short-rangereceiver that receives the packet. In certain embodiments, the hand-helddevice is a cellular telephone with a Bluetooth circuit integrateddirectly into a chipset used in the cellular telephone. In this case,the cellular telephone may include a software application that receives,processes, and displays the information. The secondary wirelesscomponent may also include a long-range wireless transmitter thattransmits information over a terrestrial, satellite, or 802.11-basedwireless network. Suitable networks include those operating at least oneof the following protocols: CDMA, GSM, GPRS, Mobitex, DataTac, iDEN, andanalogs and derivatives thereof. Alternatively, the handheld device is apager or PDA.

As shown in FIGS. 5 and 6, in yet an alternative system utilizing themonitoring device 20, a user 15 wears the monitoring device 20 on theuser's arm while exercising on exercise equipment 750. In thisembodiment, a wireless signal is transmitted to the exercise equipment750 to be displayed on a display 751 of the exercise equipment 750. Inthis embodiment, it is unnecessary for the monitoring device 20 to havea display 40 since the information is transmitted to the exerciseequipment 750. As shown in FIG. 5, a user 15 preferably wears themonitoring device 20 on her arm 72 over the radial artery.

A general method is as follows. The light source 135 transmits lightthrough at least one artery of the user. The photo-detector 130 detectsthe light. The pulse rate is determined by the signals received by thephoto-detector 130. An optical sensor 30 with a photodetector 130 andsingle LED 135 is preferably utilized. Alternatively, a pulse oximetrydevice with two LEDs and a photodetector is utilized.

This information is sent to the circuitry assembly 35 for creation ofuser's real-time pulse rate. The microprocessor 41 further processes theinformation to display pulse rate, calories expended by the user of apre-set time period, target zones of activity, time and/or dynamic bloodpressure. The information is displayed on a display member orelectro-optical display.

In a preferred embodiment, the housing 95 has three control buttons 43a-c. The control buttons 43 a-c are preferably positioned in relation tothe display member 40 to allow the user immediate visual feedback of theuser's inputted information. The middle control button 43 b preferablyactivates and deactivates the article 25. The left button 43 a ispreferably used to scroll through the different modes. The right button43 c is preferably used to input data. The control buttons 43 a-c allowfor the user's personal data to be entered and for choices to beselected by the user. The left button 43 a preferably allows for theuser's calories burned to be displayed on the display member 40 and forthe activity to be reset, and allows for other fitness monitoringfeatures to be displayed.

To activate the article 25, the middle button 43 b is depressed forpreferably 0.5 seconds and then released. The display member will appearwith a current pulse of the user and a calories burned display. Themicroprocessor preferably stores the calories burned and accumulates thevalues for a daily calories burned value and a total calories burnedvalue until the activity is reset.

To enter the user's personal data, the middle button 43 b is depressedfor 2 seconds and then released. The user will enter gender, age, mass,height and resting heart rate. Entering the data entails pushing themiddle button to select a category (gender, age, . . . ) and thenpushing the right or left button to scroll through the available optionsor to enter a value (e.g. age of the user). The middle button 43 b ispressed again to save the entry. This process is preformed until theuser's has entered all of the data that the user wishes to enter intothe microprocessor. The display member 40 will then display a heart rateand current calories burned value. A preset resting heart rate for menand women is preferably stored on the microprocessor, and used as adefault resting heart rate. However, the user may enter their ownresting heart rate value if the user is aware of that value. To accessdaily calories, the left button 43 a is pushed by the user and thedisplay member 40 will illustrate the value for daily calories burned bythe user. If the left button 43 a is pushed again, the value for totalcalories burned by the user will be displayed on the display member 40.The left button 43 a is pushed again to return to a heart rate value onthe display member 40.

The right button 43 c is pushed to scroll through the choices of otheroutput values, which comprises: basal metabolic rate; average heartrate; minimum heart rate; maximum heart rate; fat burn heart rateexercise target zone; cardio burn heart rate exercise target zone; and,summary of daily calories burned. The basal metabolic rate (displayed as“BMR”) is an estimate of the total calories burned by the user in oneday without exercise, and is based on the user inputted personal data.The average heart rate (displayed as “avHR”) is the average heart rateof the user between resets, and is an overall indicator of fitness. Thelower the average heart rate, the healthier the heart. The average heartrate is also a measure of the effectiveness of the exercise programemployed by the user since a decrease in the average heart rate of theuser will indicate the user's fitness has improved. The minimum heartrate (displayed as “mnHR”) of the user is typically measured duringsleep and periods of relaxation. The maximum heart rate (displayed as“mxHR”) is typically measured during intense workouts. The fat burnheart rate exercise target zone (displayed as “fatB”) displays a low andhigh range for the heart rate of the user to optimize fat burning duringexercise. The cardio burn heart rate exercise target zone provides ahigh and low range for the heart rate of the user to optimize cardioconditioning during exercise. The summary of daily calories burned(displayed as “cal”) displays the daily calories burned by the user.

In yet an alternative embodiment, an accelerometer, not shown, isembedded within the article 25 and connected to the circuitry assembly35 in order to provide information on the distance traveled by the user.In a preferred embodiment, the accelerometer is a multiple-axisaccelerometer, such as the ADXL202 made by Analog Devices of Norwood,Mass. This device is a standard micro-electronic-machine (“MEMs”) modulethat measures acceleration and deceleration using an array ofsilicon-based structures.

In yet another embodiment, the monitoring device 20 comprises a firstthermistor, not shown, for measuring the temperature of the user's skinand a second thermistor, not shown, for measuring the temperature of theair. The temperature readings are displayed on the display member 40 andthe skin temperature is preferably utilized in further determining thecalories expended by the user during a set time period. One suchcommercially available thermistor is sold under the brand LM34 fromNational Semiconductor of Santa Clara, Calif. A microcontroller that isutilized with the thermistor is sold under the brand name ATMega 8535 byAtmel of San Jose, Calif.

The monitoring device 20 may also be able to download the information toa computer for further processing and storage of information. Thedownload may be wireless or through cable connection. The informationcan generate an activity log or a calorie chart.

The microprocessor can use various methods to calculate calories burnedby a user. One such method uses the Harris-Benedict formula. Othermethods are set forth at www.unu.edu/unupress/food2/ which relevantparts are hereby incorporated by reference. The Harris-Benedict formulauses the factors of height, weight, age, and sex to determine basalmetabolic rate (BMR). This equation is very accurate in all but theextremely muscular (will underestimate calorie needs) and the extremelyoverweight (will overestimate caloric needs) user.

The equations for men and women are set forth below:Men: BMR=66+(13.7×mass (kg))+(5×height (cm))−(6.8×age (years))Women: BMR=655+(9.6×mass)+(1.8×height)−(4.7×age)

The calories burned are calculated by multiplying the BMR by thefollowing appropriate activity factor: sedentary; lightly active;moderately active; very active; and extra active.

Sedentary=BMR multiplied by 1.2 (little or no exercise, desk job)

Lightly active=BMR multiplied by 1.375 (light exercise/sports 1-3days/wk)

Moderately Active=BMR multiplied by 1.55 (moderate exercise/sports 3-5days/wk)

Very active=BMR multiplied by 1.725 (hard exercise/sports 6-7 days/wk)

Extra Active=BMR multiplied by 1.9 (hard daily exercise/sports &physical job or 2×day training, marathon, football camp, contest, etc.)

Various target zones may also be calculated by the microprocessor. Thesetarget zones include: fat burn zone; cardio zone; moderate activityzone; weight management zone; aerobic zone; anaerobic threshold zone;and red-line zone.Fat Burn Zone=(220−age)×60% & 70%An example for a thirty-eight year old female:(220−38)×0.6=109(220−38)×0.7=127

-   -   Fat Burn Zone between 109 to 127 heart beats per minute.        Cardio Zone=(220−your age)×70% & 80%        An example for a thirty-eight year old female:        (220−38)×0.7=127        (220−38)×0.8=146    -   Cardio zone is between 127 & 146 heart beats per minute.

Moderate Activity Zone, at 50 to 60 percent of your maximum heart rate,burns fat more readily than carbohydrates. That is the zone one shouldexercise at if one wants slow, even conditioning with little pain orstrain.

Weight Management Zone, at 60 to 70 percent of maximum, strengthens onesheart and burns sufficient calories to lower one's body weight.

Aerobic Zone, at 70 to 80 percent of maximum, not only strengthens one'sheart but also trains one's body to process oxygen more efficiently,improving endurance.

Anaerobic Threshold Zone, at 80 to 90 percent of maximum, improves one'sability to rid one's body of the lactic-acid buildup that leads tomuscles ache near one's performance limit. Over time, training in thiszone will raise one's limit.

Red-Line Zone, at 90 to 100 percent of maximum, is where seriousathletes train when they are striving for speed instead of endurance.

EXAMPLE ONE

Female, 30 yrs old, height 167.6 centimeters, weight 54.5 kilograms.

The BMR=655+523+302−141=1339 calories/day.

The BMR is 1339 calories per day. The activity level is moderatelyactive (work out 3-4 times per week). The activity factor is 1.55. TheTDEE=1.55×1339=2075 calories/day. TDEE is calculated by multiplying theBMR of the user by the activity multiplier of the user.

The heart rate may be used to dynamically determine an activity leveland periodically recalculate the calories burned based upon that factor.An example of such an activity level look up table might be as follows:

Activity/Intensity Multiplier Based on Heart RateSedentary=BMR×1.2 (little or no exercise, average heart rate 65-75 bpmor lower)Lightly active=BMR×3.5 (light exercise, 75 bpm-115 bpm)Mod. active=BMR×5.75 (moderate exercise, 115-140 pm)Very active=BMR×9.25 (hard exercise, 140-175 bpm)Extra active=BMR×13 (175 bpm−maximum heart rate as calculated with MHRformula)

For example, while sitting at a desk, a man in the above example mighthave a heart rate of between 65 and 75 beats per minute (BPM). (Theaverage heart rate for an adult is between 65 and 75 beats per minute.)Based on this dynamically updated heart rate his activity level might beconsidered sedentary. If the heart rate remained in this range for 30minutes, based on the Harris-Benedict formula he would have expended1.34 calories a minute×1.2 (activity level)×30 minutes, which is equalto 48.24 calories burned.

If the man were to run a mile for 30 minutes, with a heart rate rangingbetween 120 and 130 bpm, his activity level might be considered veryactive. His caloric expenditure would be 1.34 calories a minute×9.25(activity level)×30 minutes, which is equal to 371.85.

Another equation is weight multiplied by time multiplied by an activityfactor multiplied by 0.000119.

FIG. 10 illustrates a block diagram of a flow chart of a signalprocessing method of the present invention. As shown in FIG. 10, thephotodetector 130 of the optical sensor 30 receives light from the lightsource 135 while in proximity to the user's artery. In a preferredembodiment, the optical sensor 30 is a TRS1755 which includes a greenLED light source (567 nm wavelength) and a light-to-voltage converter.The output voltage is directly proportional to the reflected lightintensity. The signal 299 is sent to the microprocessor 41. At block1300, the signal acquisition is performed. As shown in FIG. 7, in thepulse mode the LED 135 is periodically activated for short intervals oftime by a signal from the microcontroller. The reflected pulse of lightis received by the sensor, with the generation of a voltage pulse havingan amplitude proportional to the intensity of the reflected light. Whenthe LED is activated, the switch, SW, is open by the action of thecontrol signal from the microcontroller, and the capacitor, C,integrates the pulse generated from the sensor by charging through theresistor R. Immediately prior to deactivation of the LED, theanalog-to-digital converter acquires the value of the voltage integratedacross the capacitor, C. The analog-to-digital converter generates adata sample in digital form which is utilized by the microcontroller forevaluation of the heart rate the wearer. Subsequent to the sample beingacquired by the analog-to-digital converter, the LED is deactivated andthe capacitor, C, is shortcut by switch, SW, to reset the integrator,RC. This states remains unchanged for a given time interval after whichthe process is repeated, which is illustrated in FIG. 11. A noisereduction and power reduction process is discussed below in reference toFIGS. 13 and 14.

At block 1305, a band pass filter is implemented preferably with twosets of data from the analog-to-digital converter. At block 1305, anaverage of the values of data samples within each of a first set ofsamples is calculated by the microprocessor. For example, the values ofdata samples within forty-four samples are summed and then divided byforty-four to generate an average value for the first set of samples.Next, an average of the values of data samples within a second set ofsamples is calculated by the microprocessor. For example, the values ofdata samples within twenty-two samples are summed and then divided bytwenty-two to generate an average value for the second set of samples.Preferably, the second set of samples is less than the first set ofsamples. Next, the average value of the second set of samples issubtracted from the average value for the first set of samples togenerate a first filtered pulse data value.

At block 1310, the filtered pulse data value is processed using a heartrate evaluation code to generate a first heart rate value. In apreferred method, the heart rate evaluation code obtains the heart rateby calculating the distance between crossing points of the voltagethrough zero. Once the first heart rate value is known, then an adaptiveresonant filter is utilized to generate a filtered second heart ratevalue by attenuating interference caused by motion artifacts. At block1315, a sample delay is computed as the period of evaluated heart ratedivided by two.

At block 1320, preferably a two cascade adaptive resonant filtergenerates a second filtered pulse data value which is processed at block1310 using the heart rate evaluation code to generate a second heartrate value. Those skilled in the pertinent art will recognize thatthree, four, or more, cascade adaptive resonant filters may be utilizedin generating the second filtered pulse data value. Essentially, thehighest and lowest values are disregarded in calculating the filteredsecond heart rate value. Alternatively, a phase is established and anyvalues outside of the phase are disregarded in calculating the secondheart rate value. The filtering is preferably continued during the useof the monitor thereby further refining the heart rate value of theuser.

As shown in FIG. 12, a motion sensor 1100 is included in an alternativeembodiment to assist in identifying motion noise and filtering the noisefrom the signal sent by the sensor 30. The motion sensor 1100, such asan accelerometer, is integrated into the circuitry and software of themonitoring device 20. As the motion sensor detects an arm swinging, thenoise component is utilized with the signal processing noise filteringtechniques to provide additional filtering to remove the noise elementand improve the accuracy of the monitoring device 20. More specifically,the signal from the sensor 30 is transmitted to the processor where acustom blood pressure filter 41 w processes the signal which is furtherprocessed at by custom adaptive filter 41 x before being sent to a heartbeat tracking system 41 y and then transmitted to a heart rate beatoutput 41 z. The heart rate beat output 41 z provides feedback to thecustom adaptive filter 41 x which also receives input from the motionsensor 1100.

Still further, a battery source containing twin AAA batteries is builtinto a buckle for the straps 26 a and 26 b. The battery holder ispreferably similar in appearance to a shoe buckle.

FIG. 13 illustrates a noise reduction method of the present invention.Due to the desire to minimize power consumption of the monitoring device20, and achieve very accurate signal measurements using the opticalsensor 30, the present invention preferably utilizes the method 200illustrated in FIG. 13. At block 202, the processor 41 is deactivatedfor a deactivation period in order to conserve power and to eliminatenoise for a signal measurement. The deactivation period ranges from 128to 640 microseconds, more preferably from 200 microseconds to 400microseconds, and more preferably from 225 microseconds to 300microseconds. In reference to FIG. 10, this deactivation period occursduring block 1300. At block 204, during the deactivation period, theoptical sensor 30 is activated to obtain multiple readings using thelight source 135 and the photodetector 130. Preferably 4 to 25sub-readings or sub-samples are obtained during the deactivation period.The sub-readings or sub-samples are averaged for noise reduction toprovide a reading or sample value. In a single second, from 500 to 1500sub-readings or sub-samples are obtained by the optical sensor 30. Atblock 206, the processor 41 is reactivated and the reading values areprocessed by processor 41. At block 208, heart rate data is generatedfrom the readings by the processor 41. At block 210, health related datais generated from the heart rate data, and the health related data andthe heart rate data are displayed on the display member 40.

FIG. 14 illustrates a more specific method 300 for noise reductionduring a signal reading. At block 302, a high speed clock of a processor41 is deactivated for a deactivation period as discussed above. At block304, the optical sensor 30 is activated during the deactivation periodto obtain multiple readings as discussed above. At block 306, theprocessor 41 is reactivated and the readings are processed. The opticalsensor 30 is also deactivated. At block 308, heart rate data isgenerated from the readings by the processor 41. At block 310, healthrelated data is generated from the heart rate data, and the healthrelated data and the heart rate data are displayed on the display member40.

FIG. 17 illustrates a mechanism for controlling the intensity of thelight source 135 using a plurality of resistors 405, 410 and 415 inparallel. Usually, an optical sensor 30 has a light source 135 set for asingle intensity for placement at a single location on a user. However,if the optical sensor 30 is placed at a different location, e.g. fromthe lower arm to the upper arm, the intensity of the light source 135may be too great for the photodetector 130 and lead to saturation of thephotodector 130 which terminates the signal reading. The presentinvention preferably adjusts the intensity of the light source 135 usingfeedback from the photodetector 130 to indicate whether the lightintensity is too high or too low. As shown in FIGS. 17, 17A, 17B and17C, the current flow through the resistors 405, 410 and 415 is changed,which results in changes in the light intensity of the light source 135.Equation A below illustrates the resistance:1/R _(eff) =S ₁(1/R ₁)+S ₂(1/R ₂)+S ₃(1/R ₃)where S_(n)=Switch_(n) having a value of 0 or 1, and R_(n)=resistor, inohms. IN one embedment, resistor 405 has a resistance of 400 Ohms,resistor 410 has a resistance of 200 Ohms and resistor 415 has aresistance of 100 Ohms. Various combinations of the resistors can beswitched on to control the light intensity.

FIG. 17A has current flowing through a single line and a singleresistor. FIG. 17C has current flowing through all of the lines.Although FIG. 17C utilizes the most resistors 405, 410 and 415, it hasthe greatest current flow and the highest intensity. The current flow isgiven by the equation B:(V _(cc) −V)/R _(eff) =I _(LED)where I_(LED) is the current flow. Although only three resistors areshown, those skilled in the pertinent art will recognize the more orfewer resistors may be used without departing from the scope and spiritof the present invention.

FIG. 18 is a preferred method 500 for controlling the light intensity ofthe optical sensor 30. At block 505, the light intensity of the lightsource 135 is monitored. At block 510, the sensor/phototdetector isdetermined to be saturated by the light source. At block 515, theintensity of the light source is modified by adjusting the resistanceand the flow of current to the light source 135. At block 520, the lightintensity is again monitored and adjusted if necessary. In a preferredembodiment, this automatic gain mechanism prevents the green light fromoverwhelming the photodetector thereby maintaining an accurate readingno matter where the optical sensor is placed on the user.

FIG. 19 illustrates how the control mechanism operates to maintain aproper light intensity. AS the signal reaches the upper limit, thephotodetector becomes saturated and the processor lowers the currentflow, which results in a break in the signal. Then as the signal islowered it becomes too low and the processor increases the lightintensity resulting in a break in the signal.

From the foregoing it is believed that those skilled in the pertinentart will recognize the meritorious advancement of this invention andwill readily understand that while the present invention has beendescribed in association with a preferred embodiment thereof, and otherembodiments illustrated in the accompanying drawings, numerous changesmodification and substitutions of equivalents may be made thereinwithout departing from the spirit and scope of this invention which isintended to be unlimited by the foregoing except as may appear in thefollowing appended claim. Therefore, the embodiments of the invention inwhich an exclusive property or privilege is claimed are defined in thefollowing appended claims.

1. A method of monitoring a user's vital signs, the method comprising:deactivating a processor for a deactivation period of 128 to 640microseconds; activating an optical sensor during the deactivationperiod to generate a signal corresponding to the flow of blood throughat least one artery of the user; reactivating the processor to processthe signal to obtain an average pulse value of a first set of timeperiods; processing the signal to obtain an average pulse value of asecond set of time periods, the second set of time periods less than thefirst set of time periods; subtracting the average pulse value of thesecond set of time periods from the average pulse value of the first setof time periods to generate a first filtered pulse data value;processing the first filtered pulse data value to obtain a first heartrate value; using the first heart rate value to filter the subsequentaverage pulse values generated from the digital signal to obtain areal-time heart rate value of the user; processing the real-time heartrate data of the user for analysis of real-time calories expended by theuser and for real-time display of a plurality of the user's vital signs;and displaying the plurality of user's vital signs on a display member,the display of the plurality of user's vital signs controlled by theuser using a control component.
 2. The method according to claim 1further comprising filtering motion noise from the signal utilizing amotion sensor.
 3. The method according to claim 1 wherein the opticalsensor comprises a pulsed infrared LED and a photodetector.
 4. Themethod according to claim 1 wherein the optical sensor comprises apulsed infrared LED, a green light LED and a photodetector.
 5. Themethod according to claim 1 wherein the real-time heart rate data isbased on 60 to 180 sample readings and each of the sample readings isbased on 4 to 15 sub-sample readings.